U.S. patent number 10,441,157 [Application Number 14/957,248] was granted by the patent office on 2019-10-15 for optical fiber having proximal taper for ophthalmic surgical illumination.
This patent grant is currently assigned to Novartis AG. The grantee listed for this patent is Novartis AG. Invention is credited to Alireza Mirsepassi, Ronald T. Smith.
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United States Patent |
10,441,157 |
Smith , et al. |
October 15, 2019 |
Optical fiber having proximal taper for ophthalmic surgical
illumination
Abstract
An ophthalmic illumination system can include an optical fiber
configured to transmit a light beam output by a light source and
focused by a condenser. The optical fiber can include proximal,
distal, and central portions. The proximal portion can be
configured to receive the light beam focused by the condenser. The
distal portion can be configured to emit the light beam to
illuminate a surgical field. The central portion can extend between
the proximal and distal portions. A core diameter of the proximal
portion can be larger than core diameters of the central and distal
portions. An ophthalmic illumination method can include focusing,
using a condenser, a light beam emitted by a light source onto a
proximal portion of an optical fiber. The method can also include
transmitting, using the optical fiber, the light beam to a surgical
field.
Inventors: |
Smith; Ronald T. (Fort Worth,
TX), Mirsepassi; Alireza (Fort Worth, TX) |
Applicant: |
Name |
City |
State |
Country |
Type |
Novartis AG |
Basel |
N/A |
CH |
|
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Assignee: |
Novartis AG (Lichtstrasse,
Basel, CH)
|
Family
ID: |
57590739 |
Appl.
No.: |
14/957,248 |
Filed: |
December 2, 2015 |
Prior Publication Data
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Document
Identifier |
Publication Date |
|
US 20170156581 A1 |
Jun 8, 2017 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61F
9/007 (20130101); G02B 6/0008 (20130101); A61B
3/0008 (20130101); G02B 6/0006 (20130101) |
Current International
Class: |
A61B
3/00 (20060101); A61F 9/007 (20060101); F21V
8/00 (20060101) |
Field of
Search: |
;362/572 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
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2006/088938 |
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Aug 2006 |
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WO |
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2007/053666 |
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May 2007 |
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WO |
|
Primary Examiner: Truong; Bao Q
Claims
The invention claimed is:
1. An ophthalmic illumination apparatus, comprising: a condenser;
an optical fiber having a core diameter and configured to transmit
a light beam output by a light source and focused by the condenser,
the optical fiber including: a proximal portion configured to
receive the light beam focused by the condenser onto a focal point
at the proximal portion, the proximal portion comprising a first
tapered portion comprising a proximal end having a core diameter
D.sub.1 and a terminal end having a core diameter D.sub.2, wherein
D.sub.1 is greater than D.sub.2 and a distance from the proximal
end to the terminal end of the first tapered portion is greater
than or equal to 100*(D.sub.1-D.sub.2), a distal portion configured
to emit the light beam to illuminate a surgical field, and a
central portion extending between the proximal portion and the
distal portion, wherein the core diameter is constant over the
central portion; wherein at the focal point on the proximal portion
of the optical fiber, a numerical aperture of the light beam
(NA.sub.beam) equals (a numerical aperture of the optical fiber
(NA.sub.fiber)) divided by N, wherein N equals the core diameter
D.sub.1 divided by a core diameter of the central portion; wherein:
the central portion of the optical fiber has a length in the range
of 10 millimeters (mm)-1000 mm; and the central portion is
configured such that the numerical aperture of the light beam
NA.sub.beam is equal to a numerical aperture of the central portion
NA.sub.fiber.
2. The apparatus of claim 1, wherein: the proximal portion of the
optical fiber includes a straight section positioned proximal to
the first tapered portion.
3. The apparatus of claim 1, wherein: a core diameter of the
proximal portion of the optical fiber is a multiple of the core
diameter of the central portion of the optical fiber.
4. The apparatus of claim 3, wherein: the condenser configured to
have an effective focal length based on the core diameter of the
proximal portion of the optical fiber.
5. The apparatus of claim 4, wherein: the condenser is configured
to focus the light beam such that an angular spread of the light
beam focused by the condenser is based on the core diameter of the
proximal portion of the optical fiber.
6. The apparatus of claim 4, wherein the condenser is configured to
focus the light beam such that: an angular spread of the light beam
focused by the condenser is less than an angular spread of the
light beam transmitted by the optical fiber.
7. The apparatus of claim 4, wherein the condenser is configured to
focus the light beam such that: an angular spread of the light beam
focused by the condenser is a fractional multiple of an angular
spread of the light beam transmitted by the optical fiber.
8. The apparatus of claim 1, further comprising: the light
source.
9. The apparatus of claim 8, further comprising: the condenser.
10. The apparatus of claim 9, further comprising: a surgical
instrument configured to be positioned within the surgical field
and coupled to the optical fiber.
11. The apparatus of claim 9, wherein: the light source and the
condenser are disposed within a housing.
12. An ophthalmic illumination method, the method comprising:
focusing, using a condenser, a light beam emitted by a light source
onto a focal point at a proximal portion of an optical fiber, the
optical fiber including the proximal portion, a distal portion, and
a central portion extending between the proximal portion and the
distal portion, wherein the proximal portion comprises a first
tapered portion comprising a proximal end having a core diameter
D.sub.1 and a terminal end having a core diameter D.sub.2, wherein
D.sub.1 is greater than D.sub.2; and wherein the core diameter is
constant over the central portion, wherein at the focal point on
the proximal portion of the optical fiber, a numerical aperture of
the light beam (NA.sub.beam) equals (a numerical aperture of the
optical fiber (NA.sub.fiber)) divided by N, wherein N equals the
core diameter D.sub.1 divided by a core diameter of the central
portion; and transmitting, using the optical fiber, the light beam
to a surgical field; wherein: the central portion of the optical
fiber has a length in a range of 10 mm-1000 mm; and the central
portion is configured such that the numerical aperture of the light
beam NA.sub.beam is equal to a numerical aperture of the central
portion NA.sub.fiber.
13. The method of claim 12, wherein focusing the light beam
includes: focusing the light beam onto a straight section or a
tapered section of the proximal portion of the optical fiber.
14. The method of claim 12, wherein focusing the light beam
includes: focusing the light beam using the condenser having an
effective focal length based on a core diameter of the proximal
portion of the optical fiber.
15. The method of claim 12, wherein focusing the light beam
includes: focusing the light beam using the condenser such that an
angular spread of the light beam is based on a core diameter of the
proximal portion of the optical fiber.
16. The ophthalmic illumination apparatus of claim 1, wherein: the
proximal portion comprises a straight section proximal to the first
tapered portion; and the core diameter of the fiber is constant
over the straight section of the proximal portion.
17. The ophthalmic illumination apparatus of claim 16, wherein: the
distal portion comprises a second tapered portion over which the
core diameter of the optical fiber varies distally.
18. An ophthalmic illumination apparatus, comprising: an optical
fiber having a core diameter and configured to transmit a light
beam output by a light source and focused by a condenser, the
optical fiber including: a proximal portion configured to receive
the light beam focused by the condenser onto a focal point at the
proximal portion, the proximal portion comprising a first tapered
portion in which the core diameter varies distally; a distal
portion configured to emit the light beam to illuminate a surgical
field, and a central portion extending between the proximal portion
and the distal portion, wherein the core diameter is constant over
the central portion; wherein at the focal point on the proximal
portion of the optical fiber, a numerical aperture of the light
beam (NA.sub.beam) equals (a numerical aperture of the optical
fiber (NA.sub.fiber)) divided by N, wherein N equals a core
diameter D.sub.1 divided by a core diameter of the central portion;
and wherein: the central portion of the optical fiber has a length
in a range of 10 mm-1000 mm; and the central portion is configured
such that a numerical aperture of the light beam NA.sub.beam is
equal to a numerical aperture of the central portion
NA.sub.fiber.
19. The apparatus of claim 18, wherein the core diameter of the
first tapered portion decreases distally.
20. The ophthalmic illumination apparatus of claim 18, wherein: the
proximal portion comprises a first section proximal to the first
tapered portion; and the core diameter of the fiber is constant
over the first section of the proximal portion.
21. The ophthalmic illumination apparatus of claim 18, wherein the
distal portion comprises a second tapered portion over which the
core diameter of the optical fiber varies distally.
22. The apparatus of claim 18, wherein: the core diameter of the
first tapered portion decreases distally; and the distal portion
comprises a second tapered portion over which the core diameter of
the optical fiber decreases distally.
23. The apparatus of claim 18, wherein the condenser is configured
to focus the light beam such that: an angular spread of the light
beam focused by the condenser is less than an angular spread of the
light beam transmitted by the optical fiber.
24. The apparatus of claim 18, wherein the condenser is configured
to focus the light beam such that: an angular spread of the light
beam focused by the condenser is a fractional multiple of an
angular spread of the light beam transmitted by the optical
fiber.
25. The ophthalmic illumination apparatus of claim 1, wherein a
diameter of the light beam is equal to a toleranced core diameter
of the optical fiber minus (a maximum off axis angle of collimated
beam into the condenser) times 2 times an effective focal length
for N.
26. The ophthalmic illumination method of claim 12, wherein a
diameter of the light beam is equal to a toleranced core diameter
of the optical fiber minus (a maximum off axis angle of collimated
beam into the condenser) times 2 times an effective focal length
for N.
27. The ophthalmic illumination apparatus of claim 18, wherein a
diameter of the light beam is equal to a toleranced core diameter
of the optical fiber minus (a maximum off axis angle of collimated
beam into the condenser) times 2 times an effective focal length
for N.
Description
BACKGROUND
Technical Field
Embodiments disclosed herein can be related to ophthalmic
illumination systems. More specifically, embodiments described
herein can relate to illuminating a surgical field, such as a
patient's eye, during ophthalmic procedures using an optical fiber
having a tapered proximal portion. The tapered proximal portion can
allow the optical fiber to efficiently receive a misaligned light
beam.
Related Art
Ophthalmic microsurgical procedures can require precision cutting
and/or removing of various body tissues of the patient's eye.
During the procedures, ophthalmic illumination devices can provide
light for the surgical field. A user, such as a surgeon or other
medical professional, can insert the device into the eye to
illuminate the inside of the eye. A light source and other
illumination optics, such as a collimator and a condenser, direct a
light beam towards an optical fiber of the illumination device.
During assembly of the illumination optics, manufacturers can try
to optimize various parameters of the light beam associated with
coupling the light beam into the optical fiber. For example,
coupling efficiency can be a description of coupling the light beam
into the optical fiber. High coupling efficiency can result in the
transmission of relatively greater amounts of undistorted light
from the light source to the surgical field, via the optical fiber.
Low coupling efficiency can result in to less light being
transmitted to the surgical field, as well as the light being
transmitted with an undesired angular profile. One way of improving
coupling efficiency during manufacture includes precisely aligning
the illumination optics components (e.g., the collimator, the
condenser, the optical fiber, etc.) and then immobilizing the
components so that they do not subsequently become misaligned. For
example, a beam spot of a condensed beam can be centered at the
proximal end of the optical fiber upon alignment of the condenser
and the optical fiber. However, any angular or lateral misalignment
can cause a loss of optical coupling efficiency.
The coupling efficiency into the optical fiber can be sensitive to
even small misalignments of the light beam into the condenser
and/or other components. Misalignment can arise from different
sources. Temperature changes during use can cause misalignment of a
collimated beam into the condenser. For example, the climate
surrounding the illumination optics can be atypically warm or cold,
leading to thermal-induced expansion or compression of components.
Vibration during use of the illumination optics can also cause
misalignment. The illumination optics can be subject to mechanical
shocks, such as being dropped during shipping or contacted by heavy
equipment. These sources of error can be exacerbated by the
inclusion of other optical components, such as fold mirrors and
beam splitters. Temperature changes, vibration, and/or shock can
cause the illumination optics and the light beam reflecting off of
them to become misaligned. Furthermore, over the life of the
illumination optics, slow creep of adhesive-based or
mechanical-based mounts can cause the illumination optics and the
light beam reflecting off them to become misaligned.
In some illumination optics assemblies, even angular misalignment
by as little as approximately 0.01.degree. can cause a significant
decrease in the amount of light transmitted through the optical
fiber. Because of the relatively high sensitivity to misalignment,
maintaining high fiber coupling efficiency at all temperatures and
operating conditions for the life of the illumination optics
assembly can be important. An assembly that includes means of
sensing and actively correcting for losses in fiber coupling
efficiency by moving the condenser and/or other optical components
may address some concerns. However, because of its high complexity
and cost, such a coupling-efficiency sensor and active-feedback
optical-alignment system would be difficult to design and implement
in a cost-effective manner.
Accordingly, there remains a need for improved devices, systems,
and methods that accommodate misalignment of a light beam while
maintaining high coupling efficiency by addressing one or more of
the needs discussed above.
SUMMARY
The presented solution fills an unmet medical need with a unique
solution to reduce the sensitivity of an ophthalmic illumination
system to misalignment of a light beam. The ophthalmic illumination
system can include an optical fiber having tapered proximal
portion. The tapered proximal portion can have a larger core
diameter than more distal portions of the optical fiber. The
tapered proximal portion can act as a funnel by more efficiently
coupling even misaligned light into the optical fiber. As a result,
the ophthalmic illumination system can be less sensitive to
misalignment. The ophthalmic illumination system can also include a
condenser configured to direct a condensed beam towards the optical
fiber based on the larger core diameter of the tapered proximal
portion.
Consistent with some embodiments, an ophthalmic illumination
apparatus can be provided. The apparatus can include an optical
fiber configured to transmit a light beam output by a light source
and focused by a condenser. The optical fiber can include a
proximal portion configured to receive the light beam focused by
the condenser, a distal portion configured to emit the light beam
to illuminate a surgical field, and a central portion extending
between the proximal portion and the distal portion. A core
diameter of the proximal portion can be larger than a core diameter
of the central portion and a core diameter of the distal
portion.
Consistent with some embodiments, an ophthalmic illumination method
can be provided. The method can include focusing, using a
condenser, a light beam emitted by a light source onto a proximal
portion of an optical fiber. The optical fiber can include the
proximal portion, a distal portion, and a central portion extending
between the proximal portion and the distal portion. A core
diameter of the proximal portion can be larger than a core diameter
of the central portion and a core diameter of the distal portion.
The method can also include transmitting, using the optical fiber,
the light beam to a surgical field.
Additional aspects, features, and advantages of the present
disclosure will become apparent from the following detailed
description.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a diagram illustrating an ophthalmic illumination
system.
FIG. 2A is a diagram illustrating a portion of an ophthalmic
illumination system, including an illumination subsystem and an
optical fiber.
FIG. 2B is a diagram illustrating a portion of an ophthalmic
illumination system, including an illumination subsystem and an
optical fiber.
FIG. 2C is a diagram illustrating a portion of an ophthalmic
illumination system, including an illumination subsystem and an
optical fiber.
FIG. 3 is a diagram illustrating an arrangement of a condenser and
an optical fiber.
FIG. 4 is a diagram illustrating en face views of a beam spot,
different positions of an optical fiber core when coupled to a
housing, and a toleranced core diameter that is aligned in
different positions of the optical fiber core.
FIG. 5 is a diagram illustrating an arrangement of a condenser.
FIG. 6 is a chart illustrating a figure of merit r.sub.N comparing
how much more optical misalignment can be tolerated, while
maintaining high coupling efficiency, by an optical fiber including
a tapered proximal portion relative to an optical fiber with
similarly-sized proximal and central portions.
FIG. 7 is a graph illustrating the figure of merit of FIG. 6.
In the drawings, elements having the same designation have the same
or similar functions.
DETAILED DESCRIPTION
In the following description, specific details can be set forth
describing certain embodiments. It will be apparent, however, to
one skilled in the art that the disclosed embodiments may be
practiced without some or all of these specific details. Specific
and/or illustrative, but not limiting, embodiments can be presented
herein. One skilled in the art will realize that other material,
although not specifically described herein, can be within the scope
and spirit of this disclosure.
The present disclosure describes devices, systems, and methods of
optically coupling a light beam into an optical fiber in a manner
that tolerates unintended angular or lateral misalignment of the
light beam. A light source can generate a light beam for
illuminating a surgical field, such as a patient's eye. A condenser
can focus and direct the light beam towards the optical fiber. The
condensed beam may be misaligned in some instances. The optical
fiber includes a tapered proximal portion configured to receive the
condensed beam while maintaining relatively high coupling
efficiency. The proximal portion of the optical fiber has a core
diameter that can be larger than the core diameters of the central
and distal portions. The condenser can be configured to direct the
condensed beam to the optical fiber based on the relatively larger
core diameter of the tapered proximal portion.
The devices, systems, and methods of the present disclosure provide
numerous advantages, including:
(1) The ophthalmic illumination system of the present disclosure
can better tolerate alignment errors between a light beam and a
light source, a collimator, a condenser, and/or other components of
the ophthalmic illumination system. An optical fiber with only a
straight proximal portion can be unable to accept misaligned light.
In this context, the optical fiber with the enlarged diameter
proximal portion can efficiently transmit even misaligned
light.
(2) High coupling efficiency can be maintained despite alignment
errors. The enlarged diameter proximal portion of the optical fiber
can advantageously couple light that would have otherwise been lost
due to alignment errors.
(3) Temperature-related, vibration-related, and/or shock-related
errors can be accounted for. Misalignment can result from any one
or more of these errors. By efficiently coupling even misaligned
light, the optical fiber including the enlarged diameter proximal
portion can account for multiple sources of error.
(4) The robustness of the ophthalmic illumination system to
temperature variations, vibration, and/or shock can be improved.
Even if the ophthalmic illumination system experiences these
sources of alignment error, the ophthalmic illumination system can
efficiently couple light into the optical fiber because the
enlarged diameter proximal portion accounts for the
misalignment.
(5) The lifespan of the ophthalmic illumination system can be
increased. Optical misalignment can result over the life of the
ophthalmic illumination system, including as the result of adhesive
or mechanical degradation, as well as vibration during ordinary
operation. Because the optical fiber accepts relatively greater
amounts of misaligned light, the ophthalmic illumination system can
be utilized even when the misalignment errors arise.
An ophthalmic illumination system 100 can be illustrated in FIG. 1.
The ophthalmic illumination system 100 can include a light source
122. The light source 122 can be configured to output a light beam
to illuminate a surgical field 180. The ophthalmic illumination
system 100 can also include a condenser 126 having a plurality of
lenses. The condenser 126 can be configured to focus the light beam
outputted by the light source 122. The ophthalmic illumination
system 100 can also include an optical fiber 170 configured to
transmit the light beam focused by the condenser 126. The optical
fiber 170 can include a proximal portion 172 configured to receive
the light beam focused by the condenser 126, a distal portion 174
configured to emit the light beam within the surgical field 180,
and a central portion 176 extending between the proximal portion
172 and the distal portion 174. A core diameter of the proximal
portion 172 can be larger than a core diameter of the central
portion 176 and a core diameter of the distal portion 174. The
ophthalmic illumination system 100 can also include the surgical
instrument 160 configured to be positioned within surgical field
180. The optical fiber 170 can be coupled to the surgical
instrument 160.
The ophthalmic illumination system 100 can be used during various
ophthalmic surgical procedures within the surgical field 180, such
as the patient's eye. Exemplary ophthalmic surgical procedures can
include a diagnostic procedure, a therapeutic procedure, an
anterior segment procedure, a posterior segment procedure, a
vitreoretinal procedure, a vitrectomy procedure, a cataract
procedure, and/or other suitable procedures. The surgical field 180
can include any suitable physiology of the patient's eye, including
an anterior segment, a posterior segment, a cornea, a lens, a
vitreous chamber, a retina, and/or a macula.
The surgeon can view the surgical field 180 when illuminated by
light from the light source 122. The light source 122 can be any
suitable light source operable to output a light beam optically
coupled into the optical fiber 170, as discussed herein. For
example, the light source can include a laser source, such as a
supercontinuum laser source, an incandescent light bulb, a halogen
light bulb, a metal halide light bulb, a xenon light bulb, a
mercury vapor light bulb, a light emitting diode (LED), other
suitable sources, and/or combinations thereof. The light source 122
can output a diagnostic light beam, a treatment light beam, and/or
an illumination light beam. The light beam can include any suitable
wavelength(s) of light, such as a visible light, infrared light,
ultraviolet (UV) light, etc. For example, the light beam can
transmit bright, broadband, and/or white light to illuminate the
surgical field 180.
The light beam can traverse an optical path extending between the
light source 122 and the surgical field 180, including through a
collimator 124, the condenser 126, and the optical fiber 170. The
collimator 124 can be positioned in an optical path between the
light source 122 and the surgical field 180 to receive the light
beam output by the light source 122. The collimator 124 can include
one or more lenses and/or other suitable optical components
configured to align the light beam output by the light source 122.
An optical fiber 123 that facilitates transmission of the light
beam can be mechanically and/or optically coupled with and extend
between the light source 122 and the collimator 124. The collimator
124 can collimate the light beam output by the light source 122 to
generate a collimated beam 125. The collimated beam 125 can be a
diverging, parallel, or converging beam.
The condenser 126 can be positioned in the optical path between the
light source 122 and the surgical field 180, or between the
collimator 124 and the surgical field 180, to receive the
collimated beam 125. The collimated beam 125 can be transmitted
through air or free space from the collimator 124 to the condenser
126. The condenser 126 can be configured to bend and/or otherwise
interact with the collimated light beam 125 to generate the
condensed beam 127. The condensed beam 127 can have a smaller
spatial cross-section and/or beam diameter than the collimated beam
125. In that regard, the condensed beam 127 can be a converging
beam. For example, the condenser 126 can be configured to focus the
condensed beam 127 to a beam spot 129. The condenser 126 can
include one, two, three, four, five, or more lenses and/or other
suitable optical components. Exemplary lenses can include a
biconcave lens, a biconvex lens, a convex-concave lens, a plano
concave lens, a plano convex lens, a positive/negative meniscus
lens, an aspheric lens, a converging lens, a diverging lens, and/or
combinations thereof. The condenser 126 can have any suitable lens
arrangement, including one or more singlets and one or more
doublets.
From the condenser 126, the condensed beam 127 can be transmitted
to the optical fiber 170 through air/free space or another optical
fiber. FIGS. 2A, 2B, and 2C can illustrate additional details of
the optical fiber 170. The optical fiber 170 can be configured to
transmit light from the light source 122 to the surgical field 180.
In general, as illustrated in FIG. 1, the optical fiber 170 can
include the proximal portion 172, the distal portion 174, and the
central portion 176. The proximal portion 172 can receive the
condensed beam 127 from the condenser 126. Once received at the
proximal portion 172, the light propagates distally along the
optical fiber 170 towards the surgical field 180. The central
portion 176 can extend and transmit light between the proximal
portion 172 and the distal portion 174. The distal portion 174 can
deliver emitted light 162 into the surgical field 180. At least a
portion of the optical fiber 170, such as the distal portion 174,
can be positioned within the surgical field 180. In that regard,
the optical fiber 170 can be a disposable component configured for
single use. For example, the distal portion 174 can be coupled to
the surgical instrument 160 positioned within the surgical field
180. The distal portion 174 can be disposed within or coupled to an
exterior of the surgical instrument 160. The central portion 176
and/or the proximal portion 172 can also be coupled to the surgical
instrument 160. The surgical instrument 160 can be any suitable
tool used by the surgeon during the ophthalmic surgical procedure,
including a spot illuminator, a chandelier illuminator, an
endoilluminator, an infusion cannula, a cutting probe, a vitrectomy
probe, an aspiration probe, scissors, and forceps, for example. The
surgical instrument 160 can be an infusion device 132 or a probe
152, described in greater detail below.
The light source 122, the collimator 124, and the condenser 126 can
be part of an illumination subsystem 120. The optical fiber 170 can
be in optical communication with the illumination subsystem 120.
The illumination subsystem 120 can include all or a portion of the
optical components associated with delivering light to the surgical
field 180. The illumination subsystem 120 can include various other
optical components, such as mirrors, including hot or cold dichroic
mirrors and fold mirrors, beam splitters, lenses, gratings,
filters, and/or combinations thereof, which facilitate transmission
of light to the surgical field 180. The light source 122, the
collimator 124, and the condenser 126 can be disposed within a
housing 121 of the illumination subsystem 120. The housing 121 can
be any suitable enclosure that maintains the light source 122, the
collimator 124, and the condenser 126 in a fixed arrangement
relative to one another. For example, light can be efficiently
transmitted upon alignment of the light source 122, the collimator
124, the condenser 126, and/or the optical fiber 170. The housing
121 can include a base plate. The light source 122, the collimator
124, and the condenser 126 can be mounted, affixed, and/or
otherwise mechanically coupled to the base plate so as to prevent
unintended movement of the components. As discussed herein, such
movement can adversely impact optical coupling efficiency. FIGS. 1,
2A, and 2B illustrate an unfolded optical path between the light
source 122 and the surgical field 180. The optical path can include
fold mirrors, beam splitters, and/or other optical components to
guide the light beam within the physical structure of the housing
121. Fold mirrors can allow the illumination optics to fit into a
compact volume. Beam splitters can facilitate the delivery of light
to multiple fiber ports.
Referring again to FIG. 1, the optical fiber 170 can be
mechanically coupled to the housing 121 of the illumination
subsystem 120 at a port 128. The port 128 can be a component of the
housing 121. The port 128 can be rigidly positioned relative to the
light source 122, the collimator 124, the condenser 126, and/or
other components of the illumination subsystem 120. For example,
the port 128 may include mechanical features, such as threads,
projections, grooves, to facilitate removable, mechanical coupling
between the proximal portion 172 of the optical fiber 170 and the
housing 121. The beam spot 129 of the condensed beam 127 can be
centered within the port 128. The proximal portion 172 of the
optical fiber 170 can be coupled to the housing 121 at the port
128. Proper alignment of the light source 122, the collimator 124,
the condenser 126, and/or the optical fiber 170 can ensure proper
centering of the beam spot 129 within the port 128 and efficient
coupling of the condensed beam 127 into the optical fiber 170. As
described herein, the ophthalmic surgical system 100 can be less
susceptible to degradation in optical coupling efficiency as a
result of misalignment of the light source 122, the collimator 124,
the condenser 126, and/or the optical fiber 170.
The illumination subsystem 120 can be a standalone component or
integrated in a surgical console 110. The surgeon can utilize the
surgical console 110 to control one or more parameters associated
with the ophthalmic surgical procedure. The surgical console 110
can include the illumination subsystem 120, a fluidics subsystem
130, a computing device 140, and a probe subsystem 150. One or more
components of the surgical console 110 can be coupled to and/or
disposed within a base housing 112. The base housing 112 can be
mobile such that it can be positioned proximate to the patient
during the ophthalmic surgical procedure. The base housing 112 can
include pneumatic, optical, fluid, and/or electrical supply lines
facilitating communication between components of the ophthalmic
illumination system 100.
The computing device 140 can be configured transmit control signals
to and/or receive input or status signals from one or components of
the ophthalmic illumination system 100, such as the infusion device
132, the probe 152, and/or the surgical instrument 160. For
example, the computing device 140 can control activation and
deactivation of the light source 122, as well as the intensity,
wavelength, and/or other characteristics of light output by the
light source 122. In that regard, the light source 122 and/or the
illumination subsystem 120 can be in electrical communication with
the computing device 140. The computing device 140 can include a
processing circuit having a processor 142 and a memory 144. The
processor 142 can execute computer instructions, such as those
stored on the memory 144, to control various subsystems and their
associated surgical tools. The processor 142 can be a targeted
device controller and/or a microprocessor. The memory 144, such as
semiconductor memory, RAM, FRAM, or flash memory, can interface
with the processor 142. As such, the processor 142 can write to and
read from the memory 144, and perform other common functions
associated with managing memory 144. The processing circuit of the
computing device 140 can be an integrated circuit with power,
input, and output pins capable of performing logic functions. The
computing device 140 can be in communication with a display device
146 showing data relating to system operation and performance
during an ophthalmic surgical procedure.
The fluidics subsystem 130 can be in electrical communication with
the computing device 140. The fluidics subsystem 130 can include
various components facilitating operation of an infusion device
132, such as the start/stop, rate, pressure, volume of fluid. The
infusion device 132 may deliver fluid into the patient's eye to
maintain intraocular pressure during the ophthalmic surgical
procedure. The infusion device 132 may be in fluid and/or
electrical communication with the fluidics subsystem 130.
The probe subsystem 150 can be in electrical communication with the
computing device 140. The probe subsystem 150 can include various
components facilitating operation of the probe 152. The surgeon can
utilize the probe 152 within the surgical field 180 to perform one
or more surgical maneuvers. For example, the probe 152 can be a
cutting probe, a vitrectomy probe, a phacoemulsification probe, a
laser probe, an ablation probe, a vacuum probe, a flushing probe,
scissors, forceps, an aspiration device, and/or other suitable
surgical device. The probe 152 may be in mechanical, electrical,
pneumatic, fluid, and/or other suitable communication with the
probe subsystem 150.
Portions of the ophthalmic illumination system 100, including the
illumination subsystem 120 and the optical fiber 170, can be
illustrated in FIGS. 2A, 2B, and 2C. FIGS. 2A, 2B, and 2C can
illustrate a cross-sectional view of the optical fiber 170. The
optical fiber 170 can include a core 202, cladding 204, and a
coating 206. The core 202 can be cylinder of glass, plastic,
silica, borosilicate, and/or other suitable material through which
light propagates. The cladding 204 can surround the core 202 and
confine the light within the core 202. The cladding 204 can include
a dielectric material with an index of refraction less than the
index of refraction of the core 202. The coating 206 can surround
the cladding 204 and protect the optical fiber 170 from physical
damage.
The condenser 126 can direct the focused beam 127 onto the proximal
portion 172 of the optical fiber 170. The core 202 within the
proximal portion 172 of the optical fiber 170 can include a tapered
section 210. For example, the condenser 126 can direct the focused
beam 127 onto the tapered section 210, as illustrated in FIGS. 2A
and 2B. In that regard, the diameter and the cross-sectional area
of the core 202 within the tapered section 210 can decrease
distally along the optical fiber 170. The core 202 can include an
entrance aperture 212 located at the proximal-most end of the
optical fiber 170. The entrance aperture 212 can be a part of the
core 220. For example, the entrance aperture 212 can be a proximal
face of the core 202 that interfaces with the condensed beam 127.
The entrance aperture 212 can be a part of the tapered section 210.
The entrance aperture 212 can have a diameter 214, illustrated in
FIGS. 2A and 2C. The diameter 214 of the entrance aperture 212
and/or the diameter 215 of a section 211 can be the largest
diameter of the core 202 along a length 208 of the optical fiber
170. The condensed beam 127 can be optically coupled into the
optical fiber 170 at the entrance aperture 212. For example, the
beam spot 129 can ideally be centered within the entrance aperture
212. The tapered section 210 can be similar to a funnel with an
enlarged diameter to receive the condensed beam 127.
Advantageously, the tapered section 210 can be sized and shaped to
allow high coupling efficiency by accommodating misalignment of the
beam spot 129 and/or condensed beam 127.
As illustrated in FIG. 2C, the core 202 within the proximal portion
172 of the optical fiber 170 can include a section 211 having a
constant size and shape. For example, the section 211 can be a
straight, non-tapered section. The condenser 126 can direct the
focused beam 127 onto the section 211. The section 211 can be
positioned proximally of the tapered section 210. The entrance
aperture 212 can be a part of the section 211. The section 211 can
have a diameter 215 and a length 217. The diameter 215 of the
section 211 can be substantially equal to the diameter 214 of the
entrance aperture 212. The diameter 215 and the cross-sectional
area of the section 211 can remain constant along the length 217 of
the optical fiber 170. The length 217 can be related to the
diameter 215 by a mathematical relationship. For example, the ratio
of the length 217 and the diameter 215 can be greater than one
thousand. When the length 217 and the diameter 215 satisfy this
relationship, the light within the optical fiber 170 can laterally
spread out as the light laterally fills the core 202. Thus, the
light can become spatially homogenized within the section 211,
before the light encounters the tapered region 210. This can be
true even with misalignment of the beam spot 129 and/or components
of the illumination subsystem 120 because the length 217 is
sufficiently large to allow the light to laterally spread out and
become spatially homogenized within the section 211. Thus,
advantageously, the transmittance of light through tapered section
210 can be unaffected by the misalignment of the beam spot 129
and/or components of the illumination subsystem 120 because the
light passed through the section 211 before encountering the
tapered section 210.
The core 202 within the central portion 176 of the optical fiber
170 can include a section 220 having a constant size and shape. For
example, the section 220 can be a straight, non-tapered section.
The section 220 can have a diameter 224. The diameter 224 and the
cross-sectional area of the section 220 can remain constant along
the central portion 176 of the optical fiber 170.
The core 202 within the distal portion 174 of the optical fiber 170
can include a tapered section 230. In that regard, the diameter and
the cross-sectional area of the core 202 within the tapered section
230 can decrease distally along the optical fiber 170. The tapered
section 230 can terminate at a tip 232 at the distal-most end of
the optical fiber 170. Emitted light 162 can be delivered into the
surgical field 180 via the tip 232. The tip 232 can have a diameter
234. The tapered section 230 can include a borosilicate taper, for
example. The tapered section 230 can be configured to output the
emitted light 162 with a relatively large or a relatively small
angular spread to illuminate the surgical field 180. The cladding
204 in the tapered section 230 can be stripped from the optical
fiber 170 in some examples. The core 202 within the distal portion
174 of the optical fiber 170 can have a constant size and shape in
some examples. For example, core 202 within the distal portion 174
can be a straight, non-tapered section. The core 202 within the
distal portion 174 can have a diameter that increases distally
along the optical fiber 170, in some examples. For example, the
core 202 can be a tapered section with an increasing diameter. The
core 202 within the distal portion 174 of the optical fiber 170 can
include a scattering section in lieu of or in addition to the
tapered section 230 in some examples. The tip 232 can be variously
sized and shaped, including conically-shaped, spherically-shaped,
and/or otherwise suitably shaped, to facilitate output of the
emitted light 162 within the surgical field 180 with the desired
angular spread.
The diameter of the core 202 can vary between the proximal portion
172, the central portion 176, and the distal portion 174 of the
optical fiber 170. The diameter 224 within the section 220 can be
generally described as d.sub.fiber. For example, the value of
d.sub.fiber can be between approximately 10 .mu.m and approximately
100 .mu.m, between approximately 10 .mu.m and approximately 50
.mu.m, between approximately 20 .mu.m and approximately 30 .mu.m,
including values such as 20 .mu.m, 22 .mu.m, 25 .mu.m, 27 .mu.m, 30
.mu.m, and/or other suitable values, both larger and smaller. The
diameter 214 of the entrance aperture 212 can be a multiple of the
diameter 224 and generally described as Nd.sub.fiber. The parameter
N can thus describe the larger size of the entrance aperture 212
relative to the diameter 224 of the central portion 176. The value
of the parameter N can be between 1 and 10, between 1 and 5,
between 2 and 4, including, values such as 2, 2.5, 3, 3.1, 3.3, 4,
and/or other suitable values, both larger and smaller. The value of
the parameter N can be selected to achieve improved transmission of
misaligned light while advantageously preserving a relatively small
diameter (e.g., the diameter 214) for the optical fiber 170. The
relatively small diameter of the optical fiber 170 can allow the
optical fiber 170 to be advantageously integrated in various
surgical instruments (e.g., the surgical instrument 160). The
diameter 215 of the section 211 (FIG. 2C) can be substantially
equal to the diameter 214 of the entrance aperture 212. The
diameter of the tapered section 210 within the proximal portion 172
can decrease distally from Nd.sub.fiber at the entrance aperture
212 or the section 211, to d.sub.fiber at the central portion 176.
The diameter 234 of the tip 232 can be any suitable size equal to
or smaller than d.sub.fiber of the diameter 224. The diameter 234
of the tip 232 can also be larger than d.sub.fiber of the diameter
224 in some examples. The value of diameter 234 of the tip 232 can
be between approximately 1 .mu.m and approximately d.sub.fiber of
the diameter 224, and/or other suitable values, both larger and
smaller. The diameter of the tapered section 230 within the distal
portion 174 can decrease distally from d.sub.fiber at the central
portion 176 to the diameter 234 at the tip 232. Thus, the diameter
of the core 202 within the proximal portion 172 can be larger than
the diameter of the core 202 in the central portion 176 and the
distal portion 174. The diameter of the core 202 within the central
portion 176 can be larger than the diameter of the core 202 in the
distal portion 174.
The optical fiber 170 can have any suitable length 208. For
example, the length 208 can be between approximately 0.1 m and
approximately 3 m, between approximately 1 m and 3 m, between
approximately 2.5 m and 2.6 m, including values such as 2.5 m, 2.55
m, 2.6 m, and/or other suitable vales, both larger and smaller. The
tapered section 210 of the proximal portion 172 can have a length
216. The length 216 can be any suitable length. For maximum
transmittance of light through the tapered section 210 into the
section 220, the taper can be gradual. For example, the shape of
the tapered section 210, the angle of the taper, and/or the length
216 can be selected to provide a gradual taper. For example, the
length 216 of the tapered section 210 of the proximal portion 172
can be any value that is equal to or greater than approximately one
hundred times the difference between the diameter 214 and the
diameter 224. For example, the diameter 224 can be 25 microns, and
the diameter 214 can be 75 microns (e.g., the parameter N
multiplied by the diameter 224, with N=3, or 325 .mu.m). For
maximum throughput, the length 216 can be any length longer than 5
mm (e.g., 100(75 .mu.m-25 .mu.m)). The section 220 within the
central portion 176, which has a constant shape, can have any
suitable length 226. For example, the length 226 can between
approximately 10 mm and approximately 1000 mm, between
approximately 50 mm and approximately 500 mm, between approximately
100 mm and approximately 200 mm, including values such as 100 mm,
125 mm, 145 mm, 150 mm, 166 mm, 200 mm, and/or other suitable
values both larger and smaller. The tapered section 230 of the
distal portion 174 can have any suitable length 236. For example,
the length 236 can between approximately 5 microns and
approximately 1000 microns, between approximately 5 microns and 500
microns, between approximately 10 microns and 100 microns,
including values such as 10 microns, 25 microns, 50 microns, 66
microns, 100 microns, and/or other suitable values both larger and
smaller. The core/cladding diameter ratio can remain constant or
change along the length 216 of the tapered section 210 and/or the
length 236 of the tapered section 230.
Referring now to FIG. 2B, the condenser 126 can be configured to
focus the condensed beam 127 at the beam spot 129. The beam spot
129 can be ideally centered within the port 129 and/or within the
entrance aperture 212 of the optical fiber 170. As described
herein, the entrance aperture 212 can be sized and shaped to
accommodate angular or lateral misalignment of the beam spot 129 so
as to preserve efficient optical coupling of the condensed beam 127
into the optical fiber 170. The beam spot 129 can be diffraction
limited. The beam spot 129 can have a diameter 244. The value of
the diameter 244 can be between approximately 1 .mu.m and
approximately 30 .mu.m, between 1 .mu.m and approximately 20 .mu.m,
2 .mu.m and approximately 15 .mu.m, including values such as 2
.mu.m, 8 .mu.m, 12 .mu.m, 15 .mu.m, and/or other suitable values
both larger and smaller.
The light beam originating from the light source 122 can be
characterized by its angular spread or divergence at various
locations within the optical path between the light source 122 and
the surgical field 180 (FIG. 1). A metric of the angular spread can
be the numerical aperture ("NA"). Formally, NA=sin(cone half
angle). The light beam within the ophthalmic illumination system
100 can thus be characterized by the numerical aperture
NA.sub.beam. With reference to FIG. 2B, mathematical descriptions
270 (FIG. 2B), discussed in greater detail below, describe
NA.sub.beam at various locations within the ophthalmic illumination
system 100. The optical fiber 170 can also be characterized by an
angular spread or numerical aperture NA.sub.fiber that describes
the angles of light that can be accepted and transmitted by the
optical fiber 170. The NA.sub.fiber can be a fixed characteristic
for a given optical fiber 170. Different fibers can have different
NAs. The optical fiber 170 can have any suitable numerical aperture
NA.sub.fiber, including an NA.sub.fiber between approximately 0.1
and approximately 0.9, between approximately 0.1 and approximately
0.8, between approximately 0.1 and approximately 0.7, including
values such as 0.12, 0.22, 0.26, 0.30, 0.37, 0.44, 0.48, 0.50,
0.63, 0.66, and/or other suitable values both larger and smaller.
The NA.sub.fiber can be selected such that the optical fiber 170
transmits light with the desired angular spread. When the light
beam has a numerical aperture NA.sub.beam less than or equal to the
numerical aperture NA.sub.fiber, the light beam can be transmitted
by the optical fiber 170 with little to no optical losses. With
reference to FIG. 2B, when the light beam has a numerical aperture
NA.sub.beam within the optical fiber 170 greater than the numerical
aperture NA.sub.fiber, a portion (e.g., the higher angle rays) of
the light beam can be lost in the cladding 204. Another portion
(e.g., the smaller angle rays) of the light beam that has a
numerical aperture NA.sub.beam less than or equal to the numerical
aperture NA.sub.fiber can transmitted by the optical fiber 170. In
that regard, NA.sub.beam within the optical path between the light
source 122 and the surgical field 180 can be related to the
NA.sub.fiber. The light beam at various points within the
ophthalmic illumination system 100 can also be characterized by a
beam diameter. Generally, within the optical fiber 170, the beam
diameter of the light beam can be equal to the diameter of the
optical fiber. The beam diameter and the numerical aperture
NA.sub.beam can be chosen to fill the optical fiber 170 with light
for efficient transmission to the surgical field 180.
A mathematical relationship can describe the angular spread and the
beam diameter of the light transmitted by the optical fiber 170.
For example, the product of the angular spread, such as the
NA.sub.beam, and the beam diameter can be constant. That is, the
angular spread and the beam diameter can have a reciprocal
relationship. Thus, as the beam diameter decreases, the angular
spread increases and vice versa. For example, within the tapered
region 210, as the beam diameter decreases (because the diameter of
the core 202 decreases), the angular spread of the light can
correspondingly increase. Similarly, within the tapered region 230,
the angular spread of the light can increase as the beam diameter
and the diameter of the core 202 decreases.
The mathematical descriptions 270 of the angular spread or the
NA.sub.beam at various points 254, 256, and 258 within the
ophthalmic illumination system 100 can be illustrated in FIG. 2B.
The condenser 126 can be configured to direct the condensed beam
127 to the optical fiber 170 such that that the NA.sub.beam within
the optical fiber 127 does not exceed the NA.sub.fiber. In that
regard, the NA.sub.beam of the condensed beam 127 can be based on
the diameter 214 of the entrance aperture 212. For example, the
NA.sub.beam of the condensed beam 127 can be based on the parameter
N. As described above, the diameter 214 of the entrance aperture
212 can also be related to the parameter N. The condenser 126 can
be configured to focus the condensed beam 127 such that that the
condensed beam 127 has an angular spread based on the diameter 214
of the entrance aperture 212. The point 254 can be located at the
beam spot 129, where the condensed beam 127 interfaces with the
entrance aperture 212. As shown by the mathematical relationship
270 at point 254, the condenser 126 configured to focus the
condensed beam 127 such that that
##EQU00001## The condensed beam 127 can be coupled into the optical
fiber 170 at the entrance aperture 212 having a diameter
Nd.sub.fiber. The NA.sub.beam increases by a factor of the
parameter N within the tapered region 210 as the diameter of the
202 decreases by a factor of the parameter N. The condenser 126
focusing the condensed beam 127 with
##EQU00002## thus account for the increase in angular spread or
NA.sub.beam within the tapered region 210. Accordingly, as shown by
the mathematical relationship 270 at point 256, within the central
portion 176 of the optical fiber 170, the light beam has
NA.sub.beam=NA.sub.fiber. As discussed above, efficient optical
transmission occurs within the optical fiber 170 when
NA.sub.beam=NA.sub.fiber. The NA.sub.beam increases within the
tapered region 230 as the diameter of core 202 within the distal
portion 176 decreases. The tip 232 can also be sized and shaped to
scatter or increase the angular spread of the light beam. As shown
by the mathematical relationship 270 at point 258, the optical
fiber 170 can be configured to deliver the emitted light 162 with
NA.sub.beam>>NA.sub.fiber.
The condenser 126 can have an effective focal length 246. The
effective focal length 246 can be a description of the distance the
condensed beam 127 travels between the condenser 126 and the beam
spot 129. Fold mirror(s), beam splitters, and/or other optical
components can be disposed in the optical path between the light
source 122 and the optical fiber 170, including between the
condenser 126 and the optical fiber 170. The value of the effective
focal length 246 can be between approximately 5 mm or smaller and
150 mm or greater, including values between 8 mm and 50 mm. The
condenser 126 can be positioned such that it has the effective
focal length 246 based on the diameter 214 of the entrance aperture
212 of the proximal portion 172 of the optical fiber 170.
FIG. 3 illustrates an arrangement including an optical fiber 310
and a condenser 320. In contrast to optical fiber 170 of FIGS. 1,
2A, and 2B, the optical fiber 310 of FIG. 3 does not include a
tapered proximal section. Rather, the proximal and central portions
of the optical fiber 310 have a constant diameter 312. Collimated
beam 330 can be focused by the condenser 320. A point 384
identifies a location within the arrangement of FIG. 3 where a
condensed beam 340 encounters the optical fiber 310. As shown by
mathematical relationship 370 at point 384, the condensed beam 340
can have NA.sub.beam=NA.sub.fiber. The NA.sub.beam when the
condensed beam interfaces with the optical fiber can be smaller, by
a factor of the parameter N in FIG. 2B (point 254), compared to
FIG. 3 (point 384). The light within the optical fiber 310 of FIG.
3 also has NA.sub.beam=NA.sub.fiber. The mathematical relationship
370 at point 386 illustrates that emitted light 350 can have
NA.sub.beam>>NA.sub.fiber. The condenser 320 has an effective
focal length 380.
Referring again to FIG. 2B, the effective focal length 246 of the
condenser 126 can be relatively longer than the effective focal
length 380 (FIG. 3), for equal diameters of the collimated beam 125
(FIG. 2B) and the collimated beam 330 (FIG. 3). For example, the
effective focal length 246 can be greater than the effective focal
length 380 by a factor of the parameter N. In that regard, the
effective focal length 246 can be based on the parameter N also
associated with the diameter 129 of the entrance aperture 212. The
relatively longer effective focal length 246 can allow the
NA.sub.beam to be reduced by a factor of the parameter N, at the
point 254. The condensed beam 127 can be coupled into the optical
fiber 170 at the point 254. The effective focal length 246 of the
condenser 126 can be configured to have a relatively larger
effective focal length 246 because the optical fiber 170 includes
the tapered section 210.
With reference to FIG. 2B, the shape of the light beam at points
252, 254, 256, and 258 can be illustrated in graphs 260. In that
regard, the graphs 260 include cross-sectional profile of the
irradiance of light beam on the y-axis and the radial position from
the center of the light beam on the x-axis. The illustrated light
beam can be generally Gaussian at all points 252, 254, 256, and
258. The light beam may be configured to have any suitable beam
shape, such as through use of a beam shaper positioned any point
within optical path between the light source 122 and the surgical
field 180. For example, the light beam may have a flat top beam
profile or other desired shape. The relatively narrow, small
diameter beam spot 129 can be illustrated by the relatively narrow
Gaussian profile of the graph 260 at the point 254. Graphs 360 of
FIG. 3 similarly illustrate the shape of the light beam at points
382, 384, 386 in the arrangement of the condenser 320 and the
optical fiber 310. Compared to the relatively narrow, small
diameter beam spot 129 (FIG. 2B), the Gaussian profile of the graph
360 at the point 254 can be relatively wider, indicating a
relatively larger diameter beam spot.
Referring again to FIGS. 2A and 2B, the present disclosure can
improve performance of the ophthalmic illumination system 100, such
as decreasing the sensitivity of the optical fiber 170 to
misalignment of the light source 122, the collimator 124, the
condenser 126, and/or the optical fiber 170 that occurs after
assembly of the ophthalmic illumination system 100. The factors
influencing angular sensitivity can include: (1) the diameter of
the collimated light beam 125 into the condenser 126; (2) a
toleranced core diameter of the optical fiber 170; and (3) the
mathematical relationship NA.sub.beam=NA.sub.fiber for efficient
propagation of light through the optical fiber 170. These three
factors can sometimes be difficult to change, which causes optical
misalignment sensitivity to remain high. For example, the diameter
of the collimated beam 330 can be fixed by the design of a light
source and a collimator in some instances.
Referring to FIGS. 2A and 2B, the present disclosure describes
increasing diameter of the core 202 (e.g., within the tapered
section 210) and decreasing the NA.sub.beam of the condensed beam
127 by a factor of the parameter N. Such changes can have a
positive impact on the ophthalmic illumination system 100 by
decreasing sensitivity to optical misalignment. Thus,
advantageously, the coupling efficiency can be less likely to be
decreased and/or decreases by a smaller amount as a result of
angular or lateral misalignment. An angular sensitivity parameter
.theta..sub.N can be characterized as the maximum off-axis angle of
the collimated beam 125 into the condenser 126 before significant
fiber coupling efficiency losses start to occur. A higher
.theta..sub.N corresponds to a more forgiving system for optical
misalignment because the higher off-axis angles can be efficiently
coupled into the optical fiber 170. Generally, the description
herein uses some specific example quantities so that some
calculations can be more easily understood. The specific quantities
can be exemplary only. Any suitable value can be used in different
examples.
As an approximation, .theta..sub.N can be given by:
.theta..times..times. ##EQU00003## where D.sub.N indicates the
toleranced core diameter for N, d.sub.N indicates the diameter 244
of the beam spot 129 of the condensed beam 127, and f.sub.N
indicates the effective focal length 246 for N. Some of these
variables can be graphically illustrated in FIG. 4. In that regard,
FIG. 4 can illustrate en face views of the beam spot 129, a
toleranced core 410, and different positions 432, 434, 436, and 438
of an entrance aperture of an optical fiber. The beam spot 129 can
have the diameter 244. The different positions 432, 434, 436, and
438 can represent alignment of the proximal face or entrance
aperture of the optical fiber relative to a housing or a condensed
beam. The different positions 432, 434, 436, and 438 can result
from manufacturing tolerances of the optical fiber, the housing,
and/or the port facilitating coupling between the optical fiber and
the housing. Repetition of exact positioning of the optical fiber
difficult can be difficult given the manufacturing tolerances of
the optical fiber, the housing, and/or the port. As shown, some
portions of the entrance aperture at the different positions 432,
434, 436, and 438 can overlap while others do not. A diameter 420
of the toleranced core 410 can represent consistent alignment of a
portion of the entrance aperture, relative to a condensed beam, at
each of the positions 432, 434, 436, 438. In that regard, the
entrance aperture at each of the positions 432, 434, 436, and 438
can have a diameter 430. Each of the positions 432, 434, 436, and
438 can also have an uncertainty or error associated with it,
indicated by the length 440. Generally, the diameter 420 of the
toleranced core 410 can be the difference of the diameter 430 of
the entrance apertures and the length 440 representing the position
uncertainty of the optical fibers. Despite the relatively larger
diameter 430 of the entrance aperture, the diameter 420 of the
toleranced core 410 can be relatively small. For example, the
diameter 420 of toleranced core 410 can be 7 .mu.m for an optical
fiber with an actual core diameter of 25 .mu.m.
As an approximation, the effective focal length f.sub.N for general
N can be related to the effective focal length f.sub.1 for N=1 by
f.sub.N=Nf.sub.1. In that regard, N=1 can correspond to the
arrangement of FIG. 3, in which the optical fiber does not include
a tapered proximal portion.
As an approximation, the beam spot diameter d.sub.N for general N
can be related to the beam spot size d.sub.1 for N=1 by
d.sub.N=Nd.sub.1. In that regard, the diffraction-limited (and in
general, the non-diffraction limited) beam spot diameter can be
proportional to effective focal length f.sub.N of the condenser and
therefore proportional to the parameter N. As the effective focal
length f.sub.N increases with increasing N, the beam spot diameter
d.sub.N also increases. For an optically well-designed condenser
with N=1, the diameter of the beam spot can be, at worst, only
slightly larger than the diffraction-limited spot size.
As described herein, an example of a toleranced core diameter
D.sub.N, in microns or .mu.m, can be D.sub.N=25N18. The example
term "25N" represents the actual core diameter of the entrance
aperture of the optical fiber, represented by diameter 430 in FIG.
4. The example 18 .mu.m corresponds to the uncertainty in the
position and/or alignment of the optical fiber core, represented by
length 440 in FIG. 4. The optical fiber 170 can have any suitable
core diameter, with 25 .mu.m being an example. As indicated by the
mathematical description of D.sub.N, the actual core diameter of
the entrance aperture increases by a factor of N while the
positional uncertainty remains constant. Thus, the toleranced core
diameter, which represents the portion of the optical fiber core
consistently positioned to receive the condensed beam, increases
significantly with N. For example, when N=1, D.sub.N=7 .mu.m, and
when N=3, D.sub.N=57 .mu.m. As shown with this example, the
toleranced core diameter D.sub.N increases by a factor of
approximately eight while the parameter N increases by a factor of
three. This rapid increase in the toleranced core diameter D.sub.N
with the parameter N facilitates greater tolerance of optical
misalignment in the ophthalmic illumination system 100. In that
regard, the toleranced core diameter D.sub.N increases with
increasing N faster than the beam spot diameter d.sub.N and the
effective focal length f.sub.N increase. As shown in the
calculation below, because toleranced core diameter D.sub.N
increases faster than the beam spot diameter d.sub.N and the
effective focal length f.sub.N, the angular sensitivity parameter
.theta..sub.N or the maximum off-axis angle that maintains
efficient coupling also increases.
Substituting the values for f.sub.N, d.sub.N, and D.sub.N into the
formula for .theta..sub.N yields:
.theta..times..times. ##EQU00004## For N=1, which indicates an
arrangement similar to that illustrated in FIG. 3,
.theta..times. ##EQU00005## .theta..sub.1 can be calculated by
identifying the values of d.sub.1 and f.sub.1. The root mean square
(RMS) beam spot diameter of the condensed beam 340 from the
condenser 320 or d.sub.1 can be 2.58 .mu.m, for example. The
effective focal length 380 or f.sub.1 can be calculated based on an
arrangement of the condenser 320 shown in FIG. 5. In that regard,
the effective focal length 380 can be described by
.times..times..beta. ##EQU00006## A radius a can describe the
radius of the collimated beam 330. For example, the radius a can
equal 2.65 mm. The angle .beta. can be the marginal ray angle at
the 1.3.times.1/e.sup.2 point. The angle .beta. can be
17.9.degree., for example. Inserting these values for the radius a
and the angle .beta. into the equation above, f.sub.1 or the
effective focal length 380 can be calculated to be 8.20 mm or 8200
.mu.m. The arrangement of FIG. 5 includes a beam splitter 530,
which directs the condensed beam 340 as necessary given the
physical constraints of a housing.
Inserting the example values for d.sub.1 and f.sub.1 into the
equation above for
.theta..times. ##EQU00007## mrad=0.015.degree.. Referring to FIG.
3, .theta..sub.1=0.015.degree. can describe the maximum off-axis
angle of the collimated beam 330 into the condenser 320 before
significant fiber coupling efficiency losses start to occur. The
optical fiber 310 can have a toleranced core diameter of 7 .mu.m
for an actual core diameter 312 of 25 .mu.m. The illumination
optics illustrated in FIG. 3 can have .gtoreq.72% transmittance
(manufacturing tolerances included), including diffraction
encircled energy through the 7 .mu.m toleranced core diameter and
transmittance through the angular numerical aperture of the optical
fiber 310. A maximum allowable off-axis angular error of a
collimated beam 330 into a condenser 320 of 0.0134.degree. results
in a drop in diffraction-encircled energy through the 7 .mu.m
toleranced core diameter to 90% at 650 nm. The computed
.theta..sub.1=0.015.degree. can be approximately equal to the
0.0134.degree. theoretical value calculated by optical ray tracing
using a software application, such as Zemax.
A figure of merit
.theta..theta. ##EQU00008## can gauge the how effective of the
ophthalmic system 100 of FIGS. 1, 2A, 2B, with N>1, accommodates
optical misalignment while maintaining high coupling efficiency.
The figure of merit r.sub.N compares the maximum off-axis angle
that maintains optical coupling for N>1 to the maximum off-axis
angle of N=1. More specifically,
.theta..theta..times..times..times..function. ##EQU00009## The
first term of r.sub.N can be constant with N and dependent only on
d.sub.1. The second term can be N-dependent and decrease with
increasing N for d.sub.1<7 .mu.m. In the limit of N=.infin.,
r.sub.N asymptotically approaches the first term.
Values of r.sub.N for varying N and d.sub.1 can be tabulated in
chart 600 of FIG. 6. The values of chart 600 indicate an
advantageous decrease in the post-alignment angular sensitivity of
the ophthalmic illumination system 100. In that regard, r.sub.N can
describe a multiple by which the maximum off-axis angle that
maintains efficient optical coupling increases, with N>1,
relative to the arrangement of FIG. 3, with N=1. For example, given
a RMS beam spot diameter d.sub.1 equal to 2.58 .mu.m, then,
assuming d.sub.1 equals 3 .mu.m, r.sub.N=3.25 for N=2. That is, the
maximum off-axis angle that that maintains efficient optical
coupling can be increased by a factor of 3.25 when N=2. Such a
system can be more tolerant of optical misalignment because of
efficient coupling of higher off-axis angles of light into the
optical fiber. The figure of merit r.sub.N increases to 5.5 at the
limit N=00.
FIG. 7 includes a graph 700 that plots values of r.sub.N for
varying N for different d.sub.1. The x-axis can include values of
the parameter N. The y-axis can include values of the figure of
merit r.sub.N. The curves 710, 720, and 730 correspond to d.sub.1
equal to 1 .mu.m, 2 .mu.m, and 3 .mu.m. Simulated results 740 of
actual condenser/fiber systems with parameter N values of 2, 3, 4
and 5 and with a focused beam spot size d.sub.1 of approximately
1.95 .mu.m can also be included in the graph 700. The
correspondence between the simulated results 740 and the curve 720
can be an indication of the validity of the mathematical
relationship r.sub.N.
The calculations of figure of merit r.sub.N and/or the angular
sensitivity parameter .theta..sub.N can be used by a manufacturer
to determine one or more quantities associated the ophthalmic
illumination system 110. For example, the calculations can be part
of an algorithm used to select the parameter N. The parameter N can
be used to determine the diameter 214 of the entrance aperture 212,
the effective focal length 246 of the condenser 126, the angular
spread or NA.sub.beam of the condensed beam 127, and/or other
suitable quantities. The optical fiber 170 can be manufactured or
selected based on the chosen diameter 214. The condenser 126 can be
positioned within the housing 121 relative to the light source 122,
the collimator 124, and/or the optical fiber 170, based on the
chosen effective focal length 246 and/or NA.sub.beam.
Embodiments as described herein can provide devices, systems, and
methods that facilitate greater tolerance for misalignment of the
light beam and preservation of high coupling efficiency into the
optical fiber despite the alignment errors. The examples provided
above can be exemplary in nature and not limiting. One skilled in
the art may readily devise other systems consistent with the
disclosed embodiments intended to be within the scope of this
disclosure. As such, the application can be limited only by the
following claims.
* * * * *